EP3886706B1 - Procédé et appareil pour la reconstruction et la correction d'image à l'aide d'information inter-fractionnaire - Google Patents

Procédé et appareil pour la reconstruction et la correction d'image à l'aide d'information inter-fractionnaire Download PDF

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Publication number
EP3886706B1
EP3886706B1 EP19824063.2A EP19824063A EP3886706B1 EP 3886706 B1 EP3886706 B1 EP 3886706B1 EP 19824063 A EP19824063 A EP 19824063A EP 3886706 B1 EP3886706 B1 EP 3886706B1
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Prior art keywords
fraction
scatter
scan
radiation
current
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German (de)
English (en)
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EP3886706A1 (fr
Inventor
Zhicong Yu
Chuanyong Bai
Amit Jain
Daniel Gagnon
Jacob Shea
Wenli Wang
Calvin R. MAURER, Jr.
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Accuray Inc
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Accuray Inc
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Definitions

  • aspects of the disclosed technology relate to computed tomography imaging, and in particular, to image reconstruction and correction in projection data, and, more particularly, to an apparatus and method utilizing inter-fractional information to estimate scatter in primary region projection data during computed tomography (CT) scans.
  • CT computed tomography
  • Scatter in cone-beam CT can account for a significant portion of the detected photons (including when no anti-scatter grids are used) with a wide collimation opening. Scatter can negatively impact image quality, including contrast and quantitative accuracy. Consequently, scatter measurement and scatter correction are applicable to cone-beam CT data processing and image reconstruction, including in the context of image-guided radiation treatment (IGRT).
  • IGRT can make use of medical imaging technology, such as CT, to collect images of a patient before, during, and/or after treatment.
  • the model-based methods model both a data acquisition system and the interaction process between x-rays and materials.
  • the former requires detailed knowledge of the major components of the entire imaging chain as well as information of the patient, which may be obtained from a planning CT or a first-pass reconstruction without scatter correction.
  • These methods can either be realized stochastically (e.g., Monte-Carlo-simulation based approaches) or deterministically (e.g., radiative-transfer-equation based approaches).
  • the former is computationally costly, and the latter is generally considered as an open problem in the field.
  • the model-based methods are typically patient specific and more accurate.
  • Measured x-ray projection data are considered a convolution result of the primary and the scatter kernels.
  • These methods perform a deconvolution process to separate the primary and scatter by using appropriate kernels that are established ahead of time. These methods are practical and effective to a certain extent. However, they are sensitive to the kernel design, especially in terms of material and shape of the scanned object.
  • the direct-measurement based methods such as beam-stopper-array and primary modulation. These methods are capable of measuring scatter while acquiring projection data. They do not require prior information, and thus are very robust and practical. Drawbacks of such methods include wasted dose and/or degraded image quality.
  • Another direct-measurement based method measures scatter from a shadowed region of the detector in the longitudinal direction, which is then further used for estimation of the scatter located inside the collimation opening (primary region).
  • this method is designed for a single circular scan (i.e., measurements in the primary and scatter regions occur concurrently during the same rotation), requires detector availability outside on both sides (in the longitudinal direction) of the collimation opening, and is limited in terms of estimation accuracy.
  • US2004091079 A discloses a system and method for scatter measurement and correction.
  • the method includes performing a calibration scan using a phantom to measure a scatter signal ratio between scatter x-rays impacting a first detector ring and scatter x-rays impacting a second detector ring.
  • the scatter signal ratio is used to determine a scatter scale factor.
  • the method further includes positioning a collimator such that the first detector ring is occluded from a path of primary x-rays generated by a target.
  • the method also includes executing a low exposure scan to obtain x-ray scatter data using the first detector ring and the second detector ring and applying the scatter scale factor to the scatter data to produce scaled scatter data.
  • the method further includes obtaining image data using the first detector ring and/or the said second detector ring and adjusting the image data using the scaled scatter data.
  • JP2004136021 A discloses a radiotherapy apparatus provided with first and second X-ray tubes, a detector, first and second high voltage generators for supplying electric power to the first and second X-ray tubes, a controller for controlling the second high voltage generator for the generation of therapeutic radiation from the second X-ray tube and controlling the first high voltage generator for the generation of data collecting radiation from a first radiation source.
  • a correcting device is provided for correcting data corresponding to an X-ray generating period from the first X-ray tube, with data corresponding to an X-ray stop period, and a reconstruction device for immediately reconstructing image data based on the corrected data.
  • the object of the present invention is to provide an improved imaging apparatus for radiotherapy.
  • a method of estimating scatter during imaging across multiple fractions includes receiving a previous fraction scatter measurement from a previous fraction, receiving a current fraction scatter measurement from a current fraction, wherein a scatter-to-primary ratio during the current fraction is greater than during the previous fraction, and determining a current fraction scatter estimate based on the current fraction scatter measurement and the previous fraction scatter measurement.
  • Component can be defined as a portion of hardware, a portion of software, or a combination thereof.
  • a portion of hardware can include at least a processor and a portion of memory, wherein the memory includes an instruction to execute.
  • a component may be associated with a device.
  • Logic synonymous with “circuit” as used herein, includes but is not limited to hardware, firmware, software and/or combinations of each to perform a function(s) or an action(s). For example, based on a desired application or needs, logic may include a software-controlled microprocessor, discrete logic such as an application specific integrated circuit (ASIC), or other programmed logic device and/or controller. Logic may also be fully embodied as software.
  • ASIC application specific integrated circuit
  • processor includes, but is not limited to, one or more of virtually any number of processor systems or stand-alone processors, such as microprocessors, microcontrollers, central processing units (CPUs), and digital signal processors (DSPs), in any combination.
  • the processor may be associated with various other circuits that support operation of the processor, such as random-access memory (RAM), read-only memory (ROM), programmable read-only memory (PROM), erasable programmable read-only memory (EPROM), clocks, decoders, memory controllers, or interrupt controllers, etc.
  • RAM random-access memory
  • ROM read-only memory
  • PROM programmable read-only memory
  • EPROM erasable programmable read-only memory
  • clocks decoders
  • memory controllers or interrupt controllers, etc.
  • These support circuits may be internal or external to the processor or its associated electronic packaging.
  • the support circuits are in operative communication with the processor.
  • the support circuits are not necessarily shown separate from the processor in block diagram
  • Signal includes, but is not limited to, one or more electrical signals, including analog or digital signals, one or more computer instructions, a bit or bit stream, or the like.
  • Software includes but is not limited to one or more computer readable and/or executable instructions that cause a computer, processor, logic, and/or other electronic device to perform functions, actions, and/or behave in a desired manner.
  • the instructions may be embodied in various forms such as routines, algorithms, modules, or programs including separate applications or code from dynamically linked sources or libraries.
  • a radiotherapy delivery device and method can make use of an integrated low-energy radiation source for CT for use in conjunction with or as part of IGRT.
  • a radiotherapy delivery device and method can combine a low-energy collimated radiation source for imaging in a gantry using rotational image acquisition along with a high-energy radiation source for therapeutic treatment.
  • the low-energy radiation source e.g., kV
  • the high-energy radiation source e.g., MV
  • Images generated with kV energy can have better tissue contrast than with MV energy.
  • High quality volume imaging can be needed for visualization of targets and organs-at-risk (OARS), for adaptive therapy monitoring, and for treatment planning/re-planning.
  • the kV imaging system can also be used for positioning, motion tracking, and/or characterization or correction capabilities.
  • the image acquisition methodology can include or otherwise make use of a multiple rotation scan, which may be, for example, a continuous scan (e.g., with a helical source trajectory about a central axis together with longitudinal movement of a patient support through a gantry bore), a non-continuous circular stop-and-reverse scan with incremental longitudinal movement of a patient support, etc.
  • a multiple rotation scan which may be, for example, a continuous scan (e.g., with a helical source trajectory about a central axis together with longitudinal movement of a patient support through a gantry bore), a non-continuous circular stop-and-reverse scan with incremental longitudinal movement of a patient support, etc.
  • the imaging apparatus collimates a radiation source, including, for example, into a cone beam or a fan beam using, for example, a beamformer.
  • the collimated beam can be combined with a gantry that continuously rotates while the patient moves, resulting in a helical image acquisition.
  • the time associated with increased scanning rotations to complete a high-quality volume image may be mitigated by high gantry rates/speed (e.g., using fast slip ring rotation, including, e.g., up to 10 revolutions per minute (rpm), up to 20 rpm, up to 60 rpm, or more rpm), high kV frame rates, and/or sparse data reconstruction techniques, to provide kV CT imaging on a radiation therapy delivery platform.
  • Detectors (with various row/slice sizes, configurations, dynamic range, etc.), scan pitch, and/or dynamic collimation are additional features in various embodiments, including to selectively expose portions of the detector and selectively define active readout areas.
  • a helical scan trajectory can have several advantages in view of a circular scan. For example, cone-beam artifacts are reduced because a helical scan can provide more complete projection data for image reconstruction. Also, a helical scan can acquire projection data for a large longitudinal coverage with a narrow axial opening, which could substantially reduce scatter contamination in the projection data. Reconstructed images can have significantly improved image quality in terms of low frequency artifacts and result in greatly enhanced soft-tissue contrast. Furthermore, a helical scan can improve scan speed with a large pitch.
  • an imaging apparatus 10 e.g., an x-ray imaging apparatus
  • the x-ray imaging apparatus 10 may be associated with and/or integrated into a radiotherapy device (as shown in FIG. 2 ) that can be used for a variety of applications, including, but not limited to IGRT.
  • the x-ray imaging apparatus 10 includes a rotatable gantry system, referred to as gantry 12 supported by or otherwise housed in a support unit or housing 14.
  • Gantry herein refers to a gantry system that comprises one or more gantries (e.g., ring or C-arm) capable of supporting one or more radiation sources and/or associated detectors as they rotate around a target.
  • a first radiation source and its associated detector may be mounted to a first gantry of the gantry system and a second radiation source and its associated detector may be mounted to a second gantry of the gantry system.
  • more than one radiation source and associated detector(s) may be mounted to the same gantry of the gantry system, including, for example, where the gantry system is comprised of only one gantry.
  • Various combinations of gantries, radiation sources, and radiation detectors may be combined into a variety of gantry system configurations to image and/or treat the same volume within the same apparatus.
  • kV and MV radiation sources can be mounted on the same or different gantries of the gantry system and selectively used for imaging and/or treatment as part of an IGRT system. If mounted to different gantries, the radiation sources are able to rotate independently, but are still able to simultaneously image the same (or nearly the same) volume.
  • a rotatable ring gantry 12 may be capable of 10 rpm or more, as mentioned above.
  • the rotatable gantry 12 defines a gantry bore 16 into and through which a patient can be moved and positioned for imaging and/or treatment.
  • the rotatable gantry 12 is configured as a slip ring gantry to provide continuous rotation of an imaging radiation source (e.g., x-ray) and an associated radiation detector while providing sufficient bandwidth for the high-quality imaging data received by the detector.
  • a slip-ring gantry can eliminate gantry rotations in alternating directions in order to wind and unwind cables carrying the power and signals associated with the device. Such a configuration will allow for continuous helical (e.g., fan-beam, cone-beam, etc.) computed tomography, even when integrated into an IGRT system.
  • a patient support 18 or table/couch is positioned adjacent to the rotatable gantry 12 and configured to support a patient, typically in a horizontal position, for longitudinal movement into and within the rotatable gantry 12.
  • the patient support 18 can move the patient, for example, in a direction perpendicular to the plane of rotation of the gantry 12 (along or parallel to the rotation axis of the gantry 12).
  • the patient support 18 can be operatively coupled to a patient support controller for controlling movement of the patient and patient support 18.
  • the patient support controller can be synchronized with the rotatable gantry 12 and sources of radiation mounted to the rotating gantry for rotation about a patient longitudinal axis in accordance with a commanded imaging and/or treatment plan.
  • the patient support can also be moved in a limited range up and down, left and right once it is in the bore 16 to adjust the patient position for optimal treatment.
  • the x-ray imaging apparatus 10 includes a source of imaging radiation 30 coupled to or otherwise supported by the rotatable gantry 12.
  • the source of imaging radiation 30 emits a radiation beam (indicated generally as 32) for generating high-quality images.
  • the source of imaging radiation is an x-ray source 30, configured as a kilovoltage (kV) source (e.g., a clinical x-ray source having an energy level in the range of about 20 kV to about 150 kV).
  • the kV source of radiation comprises a kilo-electron volt peak photon energy (keV) up to 150 keV.
  • the imaging radiation source can be any type of transmission source suitable for imaging.
  • the imaging radiation source may be, for example, an x-ray generating source (including for CT) or any other way to produce photons with sufficient energy and flux (such as, e.g., a gamma-source (e.g., Cobalt-57, energy peak at 122 keV), an x-ray fluorescence source (such as fluorescence source through Pb k lines, two peaks @about 70 keV and @about 82 keV), etc.).
  • a gamma-source e.g., Cobalt-57, energy peak at 122 keV
  • an x-ray fluorescence source such as fluorescence source through Pb k lines, two peaks @about 70 keV and @about 82 keV
  • References herein to x-ray, x-ray imaging, x-ray imaging source, etc. are exemplary for particular embodiments.
  • Other imaging transmission sources can be used interchangeably in various other embodiments.
  • a detector 34 (e.g., two-dimensional flat detector or curved detector) can be coupled to or otherwise supported by the rotatable gantry 12.
  • the x-ray detector 34 is positioned to receive radiation from the x-ray source 30 and can rotate along with the x-ray source 30.
  • the detector 34 can detect or otherwise measure the amount of radiation not attenuated and therefore infer what was in fact attenuated by the patient or associated patient ROI (by comparison to what was initially generated).
  • the detector 34 can detect or otherwise collect attenuation data from different angles as the x-ray source 30 rotates around and emits radiation toward the patient.
  • the x-ray detector 34 can take on a number of configurations without departing from the scope of the disclosed technology. As illustrated in FIG. 2 , the x-ray detector 34 can be configured as a flat-panel detector (e.g., a multi-row flat panel detector). In accordance with another exemplary embodiment, the x-ray detector 34 can be configured as a curved detector. The detector 34 can be adjusted to an offset (i.e., shifted) position in the channel and/or axial direction.
  • FIGS. 1 and 2 depict an x-ray imaging apparatus 10 with a radiation source 30 mounted to a ring gantry 12
  • other embodiments may include other types of rotatable imaging apparatuses, including, for example, C-arm gantries and robotic arm-based systems.
  • a gantry rotates the imaging radiation source 30 around an axis passing through the isocenter.
  • Gantry-based systems include C-arm gantries, in which the imaging radiation source 30 is mounted, in a cantilever-like manner, over and rotates about the axis passing through the isocenter.
  • Gantry-based systems further include ring gantries, for example, rotatable gantry 12, having generally toroidal shapes in which the patient's body extends through a bore of the ring/toroid, and the imaging radiation source 30 is mounted on the perimeter of the ring and rotates about the axis passing through the isocenter.
  • the gantry 12 rotates continuously.
  • the gantry 12 utilizes a cable-based system that rotates and reverses repeatedly.
  • a collimator or beamformer assembly (indicated generally as 36) is positioned relative to the x-ray source 30 to selectively control and adjust a shape of a radiation beam 32 emitted by the x-ray source 30 to selectively expose a portion or region of the active area of the x-ray detector 34.
  • the beamformer can also control how the radiation beam 32 is positioned on the x-ray detector 34.
  • the beamformer 36 could have one degree/dimension of motion (e.g., to make a thinner or fatter slit).
  • the beamformer 36 can have two degrees/dimensions of motion (e.g., to make various sized rectangles).
  • the beamformer 36 may be capable of various other dynamically-controlled shapes, including, for example, parallelograms. All of these shapes may be dynamically adjusted during a scan. In some embodiments, blocking portions of the beamformer can be rotated and translated.
  • the beamformer 36 can be controlled to adjust the shape of the radiation beam 32 emitted by the x-ray source 30 dynamically in a number of geometries, including, but not limited to, a fan beam or cone beam having a beam thickness (width) as low as one detector row width or including multiple detector rows, which will be only a portion of the detector's active area.
  • the thickness of the beam may expose several centimeters of a larger detector active area.
  • 3-4 centimeters (measured in the longitudinal direction in the detector plane) of a 5-6 centimeter detector may be selectively exposed to the imaging radiation 32.
  • 3-4 centimeters of projection image data may be captured with each readout, with about 1-2 centimeters of unexposed detector area on one or each side, which may be used to capture scatter data, as discussed below.
  • the beam thickness may be reduced down to about two centimeters, one centimeter, less than one centimeter, or ranges of similar sizes, including with smaller detectors. In other embodiments, the beam thickness may be increased to about 4 centimeters, 5 centimeters, greater than 5 centimeters, or ranges of similar sizes, including with larger detectors. In various embodiments, the ratio of exposed-to-active detector area may be 30-90% or 50-75%. In other embodiments, the ratio of exposed-to-active detector area may be 60-70%.
  • the beam and detector can be configured so that the shadowed region of the detector (active but not exposed to direct radiation) is sufficient to capture scatter data beyond the penumbra region.
  • Various embodiments may include an optimization of the features that control selective exposure of the detector 34 (e.g., beam size, beam/aperture center, collimation, pitch, detector readout range, detector readout center, etc.) such that the measured data is sufficient for primary (exposed) and shadowed regions, but also optimized for speed and dosage control.
  • the beamformer 36 shape/position and detector 34 readout range can be controlled such that the radiation beam 32 from the x-ray source 30 covers as much or as little of the x-ray detector 34 based on the particular imaging task being carried out.
  • the beam 32 can be shaped to be various shapes, including, for example, parallelograms.
  • the beamformer 36 can be configured to adjust the shape of the radiation beam 32 by rotation and/or translation of x-ray attenuated material of the beamformer 36.
  • the collimator/beamformer 36 may be configured in a variety of ways that allow it to adjust the shape of the radiation beam 32 emitted by the x-ray source 30.
  • the collimator 36 can be configured to include a set of jaws or other suitable members that define and selectively adjust the size of an aperture through which the radiation beam from the x-ray source 30 may pass.
  • the collimator 36 can include an upper jaw and a lower jaw, where the upper and lower jaws are movable in different directions (e.g., parallel directions) to adjust the size of the aperture through which the radiation beam from the x-ray source 30 passes, and also to adjust the beam position relative to the patient to illuminate only the portion of the patient to be imaged for optimized imaging and minimized patient dose.
  • the shape of the radiation beam 32 from the x-ray source 30 can be changed during an image acquisition.
  • the beamformer 36 leaf positions and/or aperture width can be adjusted before or during a scan.
  • the beamformer 36 can be selectively controlled and dynamically adjusted during rotation of the x-ray source 30 such that the radiation beam 32 has a shape with sufficient primary/shadow regions and is adjusted to include only an object of interest during imaging (e.g., the prostate).
  • the shape of the radiation beam 32 being emitted by the x-ray source 30 can be changed during or after a scan, depending on the desired image acquisition, which may be based on imaging and/or therapeutic feedback, as discussed in more detail below.
  • the x-ray imaging apparatus 10 may be integrated with a radiotherapy device that includes a therapeutic radiation source 20 coupled to or otherwise supported by the rotatable gantry 12.
  • the therapeutic radiation source 20 is configured as a source of therapeutic radiation, such as a high-energy source of radiation used for treatment of a tumor within a patient in a region of interest.
  • the source of therapeutic radiation can be a high-energy x-ray beam (e.g., megavoltage (MV) x-ray beam), and/or a high-energy particle beam (e.g., a beam of electrons, a beam of protons, or a beam of heavier ions, such as carbon) or another suitable form of high-energy radiation.
  • MV megavoltage
  • the first source of radiation 20 comprises a mega-electron volt peak photon energy (MeV) of 1 MeV or greater.
  • the high-energy x-ray beam has an average energy greater than 0.8 MeV.
  • the high-energy x-ray beam has an average energy greater than 0.2 MeV.
  • the high-energy x-ray beam has an average energy greater than 150keV.
  • the first source of radiation 20 has a higher energy level (peak and/or average, etc.) than the second source of radiation 30.
  • the therapeutic radiation source 20 is a linear accelerator (LINAC) producing therapeutic radiation (e.g., MV source) and the imaging system comprises an independent x-ray imaging source of radiation producing relatively low intensity and lower energy imaging radiation (e.g., kV source).
  • the therapeutic radiation source 20 could be a radioisotope, such as, for example, Co-60, and it can generally have energy >1 MeV.
  • the therapeutic radiation source 20 can emit one or more beams of radiation (indicated generally by 22) toward a region-of-interest (ROI) within a patient supported on the patient support 18 in accordance with a treatment plan.
  • the therapeutic radiation source 20 may be used for imaging.
  • Detector 24 can be coupled to or otherwise supported by the rotatable gantry 12 and positioned to receive radiation 22 from the therapeutic radiation source 20.
  • the detector 24 can detect or otherwise measure the amount of radiation not attenuated and therefore infer what was in fact attenuated by the patient or associated patient ROI (by comparison to what was initially generated).
  • the detector 24 can detect or otherwise collect attenuation data from different angles as the therapeutic radiation source 20 rotates around and emits radiation toward the patient.
  • the therapeutic radiation source 20 can include or otherwise be associated with a collimator.
  • the collimator associated with the therapeutic radiation source 20 can be configured in a number of ways, similar to the collimator/beamformer 36 associated with the imaging source 30.
  • a collimator/beamformer can be configured as a multi-leaf collimator (MLC), which can include a plurality of interlaced leaves operable to move to one or more positions between a minimally-open or closed position and a maximally-open position. It will be appreciated that the leaves can be moved into desired positions to achieve a desired shape of a radiation beam being emitted by the radiation source.
  • the MLC is capable of sub-millimeter targeting precision.
  • the therapeutic radiation source 20 may be mounted, configured, and/or moved into the same plane or a different plane (offset) than the imaging source 30.
  • scatter caused by simultaneous activation of the radiation sources 20, 30 may be reduced by offsetting the radiation planes.
  • x-ray imaging apparatus 10 can provide images that are used to set up (e.g., align and/or register), plan, and/or guide a radiation delivery procedure (treatment). Typical set-up is accomplished by comparing current (in-treatment) images to pre-treatment image information.
  • Pre-treatment image information may comprise, for example, computed tomography (CT) data, cone-beam CT data, magnetic resonance imaging (MRI) data, positron emission tomography (PET) data or 3D rotational angiography (3DRA) data, and/or any information obtained from these or other imaging modalities.
  • CT computed tomography
  • MRI magnetic resonance imaging
  • PET positron emission tomography
  • 3DRA 3D rotational angiography
  • the x-ray imaging apparatus 10 can track in-treatment patient, target, or ROI motion.
  • a reconstruction processor 40 can be operatively coupled to detector 24 and/or x-ray detector 34.
  • the reconstruction processor 40 is configured to generate patient images based on radiation received by the x-ray detector 34 from the x-ray source 30. It will be appreciated that the reconstruction processor 40 can be configured to be used to carry out the methods described more fully below.
  • the apparatus also includes a memory 44 suitable for storing information, including, but not limited to, processing and reconstruction algorithms and software, imaging parameters, image data from a prior or otherwise previously-acquired image (e.g., a planning image), treatment plans, and the like.
  • the x-ray imaging apparatus 10 can include an operator/user interface 48, where an operator of the x-ray imaging apparatus 10 can interact with or otherwise control the x-ray imaging apparatus 10 to provide input relating to scan or imaging parameters and the like.
  • the operator interface 48 can include any suitable input devices, such as a keyboard, mouse, voice-activated controller, or the like.
  • the x-ray imaging apparatus 10 can also include a display 52 or other human-readable element to provide output to the operator of the x-ray imaging apparatus 10.
  • the display 52 can allow the operator to observe reconstructed patient images and other information, such as imaging or scan parameters, related to operation of the x-ray imaging apparatus 10.
  • the x-ray imaging apparatus 10 includes a controller (indicated generally as 60) operatively coupled to one or more components of the apparatus 10.
  • the controller 60 controls the overall functioning and operation of apparatus 10, including providing power and timing signals to the x-ray source 30 and/or the therapeutic radiation source 20 and a gantry motor controller that controls rotational speed and position of the rotatable gantry 12.
  • the controller 60 can encompass one or more of the following: a patient support controller, a gantry controller, a controller coupled to the therapeutic radiation source 20 and/or the x-ray source 30, a beamformer 36 controller, a controller coupled to the detector 24 and/or the x-ray detector 34, and the like.
  • controller 60 is a system controller that can control other components, devices, and/or controllers.
  • the reconstruction processor 40, the operator interface 48, the display 52, the controller 60 and/or other components may be combined into one or more components or devices.
  • the apparatus 10 may include various components, logic, and software.
  • the controller 60 comprises a processor, a memory, and software.
  • an x-ray imaging apparatus and/or radiotherapy system can include various other devices and components (e.g., gantries, radiation sources, collimators, detectors, controllers, power sources, patient supports, among others) that can implement one or more routines or steps related to imaging and/or IGRT for a specific application, wherein a routine can include imaging, image-based pre-delivery steps, and/or treatment delivery, including respective device settings, configurations, and/or positions (e.g., paths/trajectories), which may be stored in memory.
  • controller(s) can directly or indirectly control one or more devices and/or components in accordance with one or more routines or processes stored in memory.
  • An example of direct control is the setting of various radiation source or collimator parameters (power, speed, position, timing, modulation, etc.) associated with imaging or treatment.
  • An example of indirect control is the communication of position, path, speed, etc. to a patient support controller or other peripheral device.
  • the hierarchy of the various controllers that may be associated with an x-ray imaging apparatus can be arranged in any suitable manner to communicate the appropriate commands and/or information to the desired devices and components.
  • the systems and methods may be implemented with other computer system configurations.
  • the illustrated aspects of the invention may be practiced in distributed computing environments where certain tasks are performed by local or remote processing devices that are linked through a communications network.
  • the reconstruction processor 40 may be associated with a separate system.
  • program modules may be located in both local and remote memory storage devices.
  • a remote database, a local database, a cloud-computing platform, a cloud database, or a combination thereof can be utilized with x-ray imaging apparatus 10.
  • X-ray imaging apparatus 10 can utilize an exemplary environment for implementing various aspects of the invention including a computer, wherein the computer includes the controller 60 (e.g., including a processor and a memory, which may be memory 44) and a system bus.
  • the system bus can couple system components including, but not limited to the memory to the processor, and can communicate with other systems, controllers, components, devices, and processors.
  • Memory can include read only memory (ROM), random access memory (RAM), hard drives, flash drives, and any other form of computer readable media.
  • Memory can store various software and data, including routines and parameters, which may comprise, for example, a treatment plan.
  • the therapeutic radiation source 20 and/or x-ray source 30 can be operatively coupled to a controller 60 configured to control the relative operation of the therapeutic radiation source 20 and the x-ray source 30.
  • the x-ray source 30 can be controlled and operated simultaneously with the therapeutic radiation source 20.
  • the x-ray source 30 can be controlled and operated sequentially with the therapeutic radiation source 20, depending on the particular treatment and/or imaging plan being implemented.
  • the x-ray source 30 and the x-ray detector 34 can be configured to provide rotation around the patient during an imaging scan in a number of ways.
  • synchronizing the motion and exposure of the x-ray source 30 with the longitudinal motion of the patient support 18 can provide a continuous helical acquisition of a patient image during a procedure.
  • continuous rotation of the radiation sources 20, 30 and detector(s) 24, 34 e.g., continuous and constant rotation of the gantry with constant patient motion speed
  • the rotatable gantry 12 and patient support can be controlled such that the gantry 12 rotates in a "back-and-forth" manner (e.g., alternating clockwise rotation and counterclockwise rotation) around a patient supported on the patient support (as opposed to continuously, as is described above) as the support is controlled to move (at a constant or variable speed) relative to the rotatable gantry 12.
  • a "back-and-forth" manner e.g., alternating clockwise rotation and counterclockwise rotation
  • movement of the patient support 18 in the longitudinal direction step
  • step alternates with a scanning revolution by the rotatable gantry 12 (shoot) until the desired volume is captured.
  • Non-continuous motion of the radiation source and/or patient support may be utilized, including in combination with the various embodiments of radiotherapy devices 10 described above.
  • Non-continuous motion of the radiation source and/or patient support continuous but variable/non-constant (including linear and non-linear) movement, speed, and/or trajectories, etc., and combinations thereof may be used, including in combination with the various embodiments of radiotherapy devices 10 described above.
  • a treatment course for a patient can comprise multiple fractions.
  • the entire treatment course as a whole can utilize inter-fractional information to optimize image reconstruction and correction, including scatter estimation. For example, this may include performing a fine scatter estimation at the beginning of the treatment course.
  • the scan configuration can gradually change for improved workflow and reduced patient dose, albeit with possibly degraded scatter measurement (i.e., an increase in the scatter-to-primary data ratio).
  • the scatter content generally increases with larger beam widths and the sampling of its distribution can become sparser (less precise) with larger beam widths, resulting in an increase in the scatter-to-primary ratio.
  • adjusting (e.g., loosening or tightening) scan configurations can affect the scatter to primary data ratio.
  • scatter measurement from a loosened configuration is associated with a higher scatter-to-primary ratio when compared to a measurement from a previous fraction
  • the quality of scatter estimation for the current fraction may still be adequate.
  • the quality of the scatter estimation with a higher scatter-to-primary ratio may be reduced but adequate, the same as a previous fraction, or improved, by combining scatter estimations from previous fractions, for at least two reasons.
  • scatter can be very low frequency and is expected to change little from fraction to fraction, and thus the very fine scatter estimation from the first fraction can still be considered as valid for the scatter of the current fraction.
  • patient information such as weight, body mass index (BMI), shape, etc.
  • BMI body mass index
  • this technique can be integrated into an adaptive workflow, where the adaptive software can flag the user that the quality of the fine scan scatter estimate is reduced.
  • the following flow charts and block diagrams illustrate exemplary configurations and methodologies associated with scatter estimation in accordance with the systems described above.
  • the exemplary methodologies may be carried out in logic, software, hardware, or combinations thereof.
  • the procedures and methods are presented in an order, the blocks may be performed in different orders, including series and/or parallel.
  • the steps below, including imaging, image-based pre-delivery steps, and treatment delivery although shown sequentially, may be executed simultaneously, including in real-time. Further, additional steps or fewer steps may be used.
  • FIG. 3 is a flow chart depicting an exemplary method 300 of scatter estimation using inter-fractional information.
  • the method 300 can consider the entire treatment course as a whole and can utilize inter-fractional information to optimize the balance between scatter estimation, patient dose, and/or workflow.
  • the method 300 can start with a fine scan configuration, such as, for example, a small helical pitch and a small beamformer opening for superior scatter estimation at the very beginning of the entire treatment course. Scatter for each fraction is estimated using the current measurement and those from previous fractions for improved estimation quality and/or stability. From fraction to fraction, the scan configuration can be loosened for improved workflow and reduced patient dose while maintaining adequate scatter estimation quality, including, for example, the same or improved scatter estimation quality.
  • the workflow can be continually adjusted (including, e.g., loosened to allow reduced quality scatter measurements or tightened to generate improved quality scatter measurements, associated with different scatter-to-primary ratios) as long as the configuration is within its limit(s), for example, at less than or equal to the maximum pitch allowed and/or at less than or equal to the maximum beamformer opening.
  • the method 300 may be sufficient for a treatment course including a smaller number of fractions (without expected significant patient changes).
  • the method 300 can begin with input 305, including initialization with a fine scan configuration.
  • a scan protocol can be well designed (e.g., tight) in favor of scatter estimation, for example, with a small opening of the beamformer and a small pitch, so that the scatter estimation is very accurate for the first fraction.
  • the time needed for this protocol may be relatively long, it can happen initially, for example, once or twice, and the impact can be considered acceptable for the entire treatment.
  • Step 310 includes scatter measurement for the current fraction
  • the scatter measurement may be in conjunction with the overall measurement and processing of projection data (including primary data) from a radiation source directed towards a target, including, for example, using a rotating radiation source for emitting a radiation beam, a detector positioned to receive radiation from the radiation source, a beamformer with a beamformer opening configured to adjust a shape of the radiation beam emitted by the radiation source, and/or a data processing system, with scan configurations and parameter settings, as described above.
  • Various scatter measurement methods may be applied, including, for example, using a beam stopper array or any of the other techniques. Note that scatter measurement of all fractions can be stored at data storage 315, and will be available for subsequent fractions if there are any.
  • data from the current fraction may be registered with one or more previous fractions.
  • this registration may be rigid or deformable, depending on practical considerations. These considerations can balance between speed, resources, and needs. While deformable registration may perform better, it can be more computationally expensive and may be more time consuming. Since the scatter is typically low frequency, a rigid registration may be sufficient for various applications. Therefore, both types of registration techniques are options and various embodiments are not limited to a specific one.
  • Data storage 315 can also be used to store registered data and registration information, as well as any other data (e.g., as needed during current and/or subsequent fractions), associated with the disclosed techniques.
  • the method can determine a scatter estimate for the current fraction based on the current fraction scatter measurement and at least one previous fraction scatter measurement. In one embodiment, this includes determining an intra-fraction scatter estimate based on the current fraction scatter measurement, determining an inter-fraction scatter estimate based on at least one previous fraction scatter measurement and a relationship between scatter and a scan parameter setting (e.g., where a current fraction scan configuration comprises at least one scan parameter setting different than a previous scan configuration), and determining the current fraction scatter estimate by combining the intra-fraction scatter estimate and the inter-fraction scatter estimate.
  • a scan parameter setting e.g., where a current fraction scan configuration comprises at least one scan parameter setting different than a previous scan configuration
  • Step 330 can include optimization processes using data from both current and previous fractions. For example, an optimization process can be used for determining an improved estimation of scatter, primary, and/or a scatter-to-primary ratio (SPR). This optimization can consider both intra-fractional and inter-fractional (if available) information. For example, for the current fraction, step 330 can first estimate scatter, primary, and/or SPR information using intra-fractional information based on a selected technique. Then, assuming that there is an inherent relationship between fractions in terms of scatter information, the data can be improved or optimized.
  • SPR scatter-to-primary ratio
  • the optimization can perform a fitting process for SPR against the opening of the beamformer across different fractions.
  • FIG. 7 shows an exemplary linear relationship between beamformer opening and SPR for a phantom and lung plus fat layers.
  • Various other relationships between scan parameter settings and scatter measurements can be used, including with use of non-linear fitting techniques. Such a process can also be used to exclude inaccurate scatter measurements that occurred due to, for example, an abrupt change of anatomy involved in views used for scatter estimation.
  • the method 300 determines if the scan configuration can be loosened, for example, to improve workflow or reduce patient dose, albeit by allowing a higher scatter-to-primary ratio.
  • Configuration limits for scan parameters settings can be set to maintain a minimum level of scatter measurement quality during the loosening process.
  • the method determines if one or more configuration limits (e.g., associated with scan parameter settings) have been reached. In conjunction with improving workflow and reducing patient dose, a certain quality of scatter measurement (e.g., a maximum SPR) must be maintained.
  • scan parameter configuration limits can be set such that the associated scatter measurement meets a minimum image quality requirement depending on the needs of the application.
  • step 350 adjusts the scan configuration. This step is only performed if it is determined that further loosening of the scan configuration will not degrade the quality of the ultimate scatter estimation below a minimum level. Adjustments to scan parameter settings can be in accordance with any suitable algorithm or technique, including, for example, based on predetermined increments along linear or non-linear trajectories, percentages of remaining allowance before reaching configuration limit, combinations of parameter setting values (e.g., beamformer opening dependent on pitch/step size or vice versa), patient characteristics (e.g., BMI), combinations thereof, etc.
  • any suitable algorithm or technique including, for example, based on predetermined increments along linear or non-linear trajectories, percentages of remaining allowance before reaching configuration limit, combinations of parameter setting values (e.g., beamformer opening dependent on pitch/step size or vice versa), patient characteristics (e.g., BMI), combinations thereof, etc.
  • adjustments can be limited to apply to a small number of parameters, such as, for example, beamformer opening, patient support movement step size or effective pitch, etc. In various embodiments, adjustments can avoid changing other parameters, such as, for example, tube current, potential, filters, rotation time, etc.
  • loosening a scan parameter setting for a subsequent fraction at step 350 is based on current fraction data and previous fraction data, where a subsequent fraction scatter measurement is associated with a higher SPR versus the current fraction scatter measurement because of the loosened scan parameter setting.
  • adjusting scan parameter settings for a subsequent fraction includes optimizing scatter estimation quality, workflow, and/or patient dose across different fractions in accordance with various priorities associated with the application/treatment. For example, the configuration limits and/or adjustments mentioned above can all be weighted differently to optimize or balance quality, time, and/or dose to different degrees in different situations.
  • step 360 the scan configuration for the next fraction is preserved or maintained without further loosening or degradation in quality.
  • the method then proceeds with the next fraction scatter measurement at step 310, continuing until the treatment is complete.
  • FIG. 4 is a flow chart depicting another exemplary method 400 of scatter estimation using inter-fractional information.
  • the method 400 can consider the entire treatment course as a whole and can utilize inter-fractional information to optimize the balance between scatter estimation, patient dose, and/or workflow.
  • method 400 adds consideration of changes in the patient that may require a tightening or re-set of the scan configuration. For example, this may occur in situations where a patient change would reduce the applicability of prior fractions' scatter measurements to the current patient situation.
  • This method 400 may be viewed as consisting of an inner loop adjusting the scan configuration similar to method 300 and an outer loop monitoring the patient information, for example, where the inner loop is a component of the outer loop.
  • the method 400 can start with a fine scan configuration, such as, for example, a small helical pitch and a small beamformer opening for superior scatter estimation at the very beginning of the entire treatment course.
  • a fine scan configuration such as, for example, a small helical pitch and a small beamformer opening for superior scatter estimation at the very beginning of the entire treatment course.
  • scatter for each fraction is estimated using the current measurement and those from available previous fractions for improved estimation quality and stability.
  • the scan configuration can be adjusted (e.g., loosened) for improved workflow and reduced patient dose, while maintaining the same or improved scatter estimation quality.
  • the workflow can be continually adjusted as long as the configuration is within its configuration limit(s) for various scan parameter settings. For example, at less than or equal to the maximum pitch allowed and/or at less than or equal to the maximum beamformer opening.
  • the outer loop is designed to monitor patient information, including, for example, body mass index (BMI), to improve the stability of the method 400. If a substantial patient information or characteristic change is determined, for example, by comparing a measurable to a threshold, the scan configuration can be tightened or reset to a fine scan configuration before starting another inner loop.
  • BMI body mass index
  • the workflow may stay within the inner loop (e.g., as in method 300 described above) for a treatment course including a smaller number of fractions (without expected significant patient changes).
  • the outer loop may be utilized for a treatment course including a larger number of fractions depending on the amount of change occurring to the patient during the treatment course.
  • the method 400 determines if the scan configuration can be loosened, for example, to improve workflow or reduce patient dose, albeit by allowing a higher scatter-to-primary ratio. If one or more scan parameter settings have not yet reached their respective configuration limits, the method proceeds to step 350 and adjusts the scan configuration.
  • step 460 to check patient information.
  • Patient information can be used to monitor the amount of change that has occurred in the patient, such as, for example, shape, weight, BMI, etc.
  • Various thresholds can be defined so that if the amount of change of the monitored information exceeds a certain threshold (e.g., a 10% change in BMI), then the next fraction can include a scan configuration with tightened or reset scan parameter settings, resulting in a lower SPR.
  • determining if the patient information has exceeded the threshold can be based on one measurable, a plurality of measurables, and/or combinations of measurables, including where measurables have different weights and/or priorities.
  • step 480 to reset the scan configuration by adjusting a scan parameter setting for a subsequent fraction such that the next fraction scatter measurement is improved versus the previous fraction scatter measurement because of the adjusted scan parameter setting.
  • re-setting the scan configuration includes starting the next fraction with a fine scan configuration at step 305, to re-estimate scatter with improved accuracy or quality.
  • the re-configuration can go back to that of the first fraction or can be adjusted (e.g., tightening) with a dedicated algorithm to improve the scatter measurement quality, depending on the application.
  • step 470 the scan configuration for the next fraction is preserved or maintained without loosening or tightening to adjust the scatter measurement quality.
  • the method then proceeds with the next fraction scatter measurement at step 310, continuing until the treatment is complete.
  • determining if a scan parameter setting for the current fraction is less than a scan parameter limit and determining if a patient characteristic exceeds a characteristic threshold can be executed in different orders and at different times in various embodiments.
  • FIG. 5 is a flow chart depicting another exemplary method 500 of scatter estimation using inter-fractional information.
  • step 540 determines if patient information has exceeded a threshold before the configuration limits are checked.
  • the method 500 proceeds to step 550 to determine if the available scan parameter settings have reached their respective configuration limits. As discussed above, if the available scan parameter settings have not reached their respective configuration limits, the method proceeds to step 560 to adjust the scan configuration (e.g., loosening scan parameter settings). If the available scan parameter settings have reached their respective configuration limits, the method proceeds to step 570, preserving the current configuration.
  • step 580 the method 500 proceeds to step 580 to reset the scan configuration as discussed above.
  • the other steps can be implemented similar to the steps of method 300.
  • FIG. 6 is a flow chart depicting another exemplary method 600 of scatter estimation using inter-fractional information.
  • step 670 determines if patient information has exceeded a threshold before the current fraction scatter measurement at step 310.
  • step 310 measure the current fraction scatter, as discussed above. If the patient information exceeds a threshold, the method 600 proceeds to step 680 to reset the scan configuration as discussed above.
  • step 680 to reset the scan configuration as discussed above. The remaining steps can be implemented similar to the steps of method 300.
  • FIG. 8 is a flow chart depicting an exemplary method 800 of scatter estimation and correction using inter-fractional data, such as those described above.
  • Inputs can include any optional prior data and/or scan designs.
  • step 810 includes data acquisition. For example, during rotation of a radiation source projecting a collimated radiation beam towards a target and radiation detector, the method measures projection data (primary + scatter) during a current fraction, in accordance with any of the embodiments described above.
  • Data acquisition in step 810 can also include adjusting a shape/position of the radiation beam with the beamformer before and/or during the scan.
  • Adjusting the radiation beam with the beamformer can include rotation and translation of highly attenuated material of the beamformer during the scan to change the shape/size of the radiation beam, including to generate more or less scatter during the scan.
  • step 820 includes scatter estimation.
  • the method estimates the scatter in the projection data using scatter measurements from the current and previous fraction(s), in accordance with any of the embodiments described above.
  • step 830 includes scatter correction.
  • scatter estimated from step 820 is subtracted from the projection data to obtain scatter corrected projection data.
  • Output includes scatter corrected projection data suitable for imaging.
  • Various embodiments can utilize different scan geometries, detector positioning/active areas, beamformer positioning/window shapes, etc.
  • FIG. 9 is a flow chart depicting an exemplary method 900 of scatter estimation and correction using inter-fractional data, such as those described above.
  • Inputs can include any optional prior data and/or scan designs.
  • step 910 includes data acquisition during fraction 1, which can be a previous fraction, where the method measures projection data (primary + scatter) during fraction 1.
  • step 920 the method adjusts a scan parameter setting of the scan configuration based on the measured scatter, previous configuration settings, and/or patient information, as described above. For example, step 920 can adjust the beamformer opening and/or scan pitch/step size.
  • step 930 includes data acquisition during fraction 2, where the method measures projection data (primary + scatter) during fraction 2.
  • the method can combine the measured scatter data from fraction 1 and fraction 2, including with use of various model fitting techniques.
  • step 950 includes scatter estimation, where the method estimates the scatter in the projection data for fraction 2 using the scatter measurements from fraction 1 and fraction 2.
  • step 960 includes scatter correction, where the method subtracts the estimated scatter from the projection data to obtain scatter corrected projection data.
  • Output includes scatter corrected projection data suitable for imaging.
  • steps of method 900 can be implemented in accordance with any of the embodiments described above.
  • One or more optimization processes are also applicable to all of the above embodiments to determine scan parameters, adjustments, limits, thresholds, etc.
  • FIG. 10 is a flow chart depicting an exemplary method 1000 of IGRT using a radiotherapy device (including, e.g., x-ray imaging apparatus 10).
  • Prior image data 1005 of the patient may be available for use, which may be a previously-acquired planning image, including a prior CT image.
  • Prior data 1005 can also include treatment plans, phantom information, models, a priori information, etc.
  • prior image data 1005 is generated by the same radiotherapy device, but at an earlier time.
  • prior image data 1005 can also include data from previous fractions.
  • imaging of a patient is performed using a source of low-energy radiation (e.g., kV radiation from x-ray source 30).
  • a source of low-energy radiation e.g., kV radiation from x-ray source 30.
  • imaging comprises a helical scan(s) with a fan or cone beam geometry.
  • Step 1010 can produce high-quality (HQ) image(s) or imaging data 1015 using the projection data processing techniques described above.
  • image quality may be adjusted to optimize a balance between image quality/resolution and dosage. In other words, not all images need to be of the highest quality or image quality may be adjusted to optimize or trade off a balance between image quality/resolution and image acquisition time.
  • Imaging step 1010 can also include image processing to generate patient images based on the imaging data (e.g., in accordance with the methods described above).
  • image processing step 1020 is shown as part of imaging step 1010, in some embodiments image processing step 1020 is a separate step, including where image processing is executed by separate devices.
  • step 1030 one or more image-based pre-delivery steps, discussed below, are performed based at least in part on the imaging data 1015 from step 1010.
  • step 1030 can include determining various parameters associated with the therapeutic treatment and (subsequent) imaging planning.
  • image-based pre-delivery steps (1030) may require more imaging (1010) before treatment delivery (1040).
  • Step 1030 can include adapting a treatment plan based on the imaging data 1015 as part of an adaptive radiotherapy routine.
  • image-based pre-delivery steps 1030 may include real-time treatment planning.
  • Embodiments may also include simultaneous, overlapping, and/or alternating activation of the imaging and therapeutic radiation sources. Real-time treatment planning may involve any or all of these types of imaging and therapeutic radiation activation techniques (simultaneous, overlapping, and/or alternating).
  • Step 1040 therapeutic treatment delivery is performed using a source of high-energy radiation (e.g., MV radiation from therapeutic radiation source 20).
  • Step 1040 delivers a treatment dose 1045 to the patient according to the treatment plan.
  • the IGRT method 1000 may include returning to step 1010 for additional imaging at various intervals, followed by image-based pre-delivery steps (1030) and/or treatment delivery (1040) as required.
  • the high-quality imaging data 1015 may be produced and utilized during IGRT using one apparatus 10 that is capable of adaptive therapy.
  • steps 1010, 1020, 1030, and/or 1040 may be executed simultaneously, overlapping, and/or alternating.
  • IGRT can include at least two general goals: (i) to deliver a highly conformal dose distribution to the target volume; and (ii) to deliver treatment beams with high accuracy throughout every treatment fraction.
  • a third goal can be to accomplish the two general goals in as little time per fraction as possible.
  • Delivering treatment beams accurately requires the ability to identify and/or track the location of the target volume intrafraction with high-quality images.
  • the ability to increase delivery speed requires the ability to accurately, precisely, and quickly move the radiation source according to the treatment plan.
  • FIG. 11 is a block diagram 1100 depicting exemplary image-based pre-delivery steps/options that may be associated with step 1030 above.
  • the above-described x-ray imaging apparatus 10 e.g., as part of a radiotherapy device
  • images 1015 generated by the radiotherapy device can be used to align a patient prior to treatment (1110).
  • Patient alignment can include correlating or registering the current imaging data 1015 with imaging data associated with earlier pre-treatment scans and/or plans, including the treatment plan.
  • Patient alignment can also include feedback on the physical position of the patient relative to the radiation source to verify whether the patient is physically within the range of the delivery system. If necessary, the patient can be adjusted accordingly.
  • patient alignment imaging may purposely be of lesser quality to minimize dosage but provide adequate alignment information.
  • Images generated by the x-ray imaging apparatus 10 can also be used for treatment planning or re-planning (1120).
  • step 1120 can include confirming the treatment plan, modifying the treatment plan, generating a new treatment plan, and/or choosing a treatment plan from a set of treatment plans (sometimes referred to as "plan of the day"). For example, if the imaging data 1015 shows that the target volume or ROI is the same as when the treatment plan was developed, then the treatment plan can be confirmed. However, if the target volume or ROI is not the same, re-planning of the therapeutic treatment may be necessary.
  • the imaging data 1015 may be used for treatment planning or re-planning (e.g., generating a new or modified treatment plan). In this manner, pre-treatment CT imaging via a different device is not necessary. In some embodiments, confirming and/or re-planning may be an ongoing procedure before and/or after various treatments.
  • images generated by the x-ray imaging apparatus 10 can be used to calculate imaging dose (1130), which may be used for ongoing determinations of total dose to the patient and/or for subsequent imaging planning. The quality of subsequent imaging may also be determined as part of the treatment planning, for example, to balance quality and dosage.
  • images generated by the x-ray imaging apparatus 10 can be used to calculate treatment dose (1140), which may be used for ongoing determinations of total dose to the patient and/or may be included as part of treatment planning or re-planning.
  • images generated by the x-ray imaging apparatus 10 can be used in connection with planning or adjusting other imaging (1150) and/or other treatment (1160) parameters or plans, including, for example, as part of adaptive therapy and/or treatment plan generation.
  • images generated by the x-ray imaging apparatus 10 can be used in connection with adaptive therapy monitoring (1170), which can include monitoring treatment delivery and adapting as required.
  • calculate treatment dose (1140) can be a step by itself and/or can be part of adaptive therapy monitoring (1170) and/or treatment planning (1120).
  • the image-based pre-delivery steps (1030) can be performed automatically and/or manually with human involvement.
  • FIG. 12 is a block diagram 1200 depicting exemplary data sources that may be utilized during imaging (1010) and/or subsequent image-based pre-delivery steps (1030).
  • Detector data 1210 represents all of the data received by the image radiation detector 34.
  • the projection data 1220 is the data generated by the radiation incident in the collimated beam area.
  • the penumbra data 1230 is the data generated by the radiation incident in the penumbra area.
  • the scatter data 1240 is the data generated by the radiation incident in the peripheral area outside of the penumbra area, which may be referred to as the shadow region(s). In some embodiments, scatter data can be generated separate from or in addition to the radiation incident in the shadow regions of the detector.
  • the penumbra data 1230 may be used to separate or identify the projection and/or scatter data.
  • the scatter data 1240 can be used to estimate the scatter radiation in the projection data 1220.
  • the scatter data 1240 can be used to determine the residual effect of the scatter from the therapeutic radiation source 20 (e.g., MV) when the two sources 20, 30 are operated simultaneously or in an interleaved manner.
  • the penumbra data 1230 and/or the scatter data 1240 may be utilized to improve the quality of the images generated by the imaging step 1010.
  • the penumbra data 1230 and/or the scatter data 1240 may be combined with the projection data 1220 and/or analyzed in view of the applicable imaging settings 1250, treatment settings 1260 (e.g., if simultaneous imaging and treatment radiation), and any other data 1270 associated with the x-ray imaging apparatus 10 at the time of the data collection at the imaging detector 34.
  • the data may be used for the treatment planning step 1030.

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Claims (11)

  1. Appareil d'imagerie destiné à l'imagerie à travers de multiples fractions, comprenant :
    une source de rayonnement rotative pour émettre un faisceau de rayonnement ;
    un détecteur positionné pour recevoir un rayonnement de la source de rayonnement ;
    un système de traitement de données conçu pour :
    recevoir (305) une mesure précédente de diffusion de fraction à partir d'une fraction précédente ;
    recevoir (310) une mesure présente de diffusion de fraction à partir d'une fraction présente,
    un ratio de diffusion par rapport à primaire durant la fraction présente étant supérieur à celui durant la fraction précédente ; et
    déterminer (330) une estimation présente de diffusion de fraction sur la base de la mesure présente de diffusion de fraction et de la mesure précédente de diffusion de fraction,
    une configuration de balayage de la fraction présente étant assouplie par rapport à une configuration de balayage de la fraction précédente, la configuration assouplie de balayage étant associée à un ratio supérieur de diffusion par rapport à primaire par rapport au ratio de diffusion par rapport à primaire pour la fraction précédente.
  2. Appareil selon la revendication 1, le réglage des paramètres de balayage étant basé sur un plan de traitement et une caractéristique du patient.
  3. Appareil selon la revendication 1, une configuration précédente du balayage de fraction comprenant des réglages de paramètres de balayage associés à une configuration de balayage fin.
  4. Appareil selon la revendication 1, comprenant en outre :
    un formeur de faisceau comprenant une ouverture du formeur de faisceau conçue pour ajuster une forme du faisceau de rayonnement émis par la source de rayonnement ;
    l'ouverture du formeur de faisceau durant la fraction présente étant plus grande que l'ouverture du formeur de faisceau durant la fraction précédente.
  5. Appareil selon la revendication 1, un pas d'un balayage hélicoïdal ou une taille de pas d'un balayage circulaire durant la fraction présente étant plus grand·e que le pas ou que la taille de pas durant la fraction précédente.
  6. Appareil selon la revendication 1, le système de traitement de données étant en outre conçu pour :
    déterminer si un réglage des paramètres de balayage pour la fraction présente est inférieur à une limite des paramètres de balayage ;
    si le réglage des paramètres de balayage pour la fraction présente est inférieur à la limite des paramètres de balayage, alors un ajustement du réglage des paramètres de balayage pour une fraction ultérieure, le ratio de diffusion par rapport à primaire durant la fraction ultérieure étant supérieur à celui durant la fraction présente sur la base du réglage ajusté des paramètres de balayage ; et
    si le réglage des paramètres de balayage pour la fraction présente n'est pas inférieur à la limite des paramètres de balayage, alors le maintien du réglage des paramètres de balayage pour la fraction ultérieure.
  7. Appareil selon la revendication 1, une détermination de l'estimation présente de diffusion de fraction comprenant :
    une détermination d'une estimation de diffusion intra-fractionnaire sur la base de la mesure présente de diffusion de fraction ;
    une détermination d'une estimation de diffusion inter-fractionnaire sur la base d'au moins une mesure précédente de diffusion de fraction et d'une relation entre une diffusion et un réglage des paramètres de balayage, une configuration présente de balayage de fraction comprenant au moins un réglage des paramètres de balayage différent d'une configuration précédente de balayage ; et
    une détermination de l'estimation présente de diffusion de fraction sur la base de l'estimation de diffusion intra-fractionnaire et de l'estimation de diffusion inter-fractionnaire.
  8. Appareil selon la revendication 1, le système de traitement de données étant en outre conçu pour :
    déterminer si une caractéristique d'un patient excède un seuil de caractéristique ; et
    si la caractéristique du patient excède le seuil de caractéristique, alors ajuster un réglage des paramètres de balayage pour une fraction suivante, le ratio de diffusion par rapport à primaire durant la fraction suivante étant inférieur à celui durant une fraction précédente sur la base du réglage ajusté des paramètres de balayage.
  9. Appareil selon la revendication 8, l'ajustement du réglage des paramètres de balayage comprenant un nouveau réglage du réglage des paramètres de balayage à un réglage initial associé à une configuration initiale de balayage.
  10. Appareil selon la revendication 1, le système de traitement de données étant en outre conçu pour :
    déterminer si un réglage des paramètres de balayage pour la fraction présente est inférieur à une limite des paramètres de balayage ;
    si le réglage des paramètres de balayage pour la fraction présente est inférieur à la limite des paramètres de balayage, alors ajuster le réglage des paramètres de balayage pour une fraction ultérieure, le ratio de diffusion par rapport à primaire durant la fraction ultérieure étant supérieur à celui durant la fraction présente sur la base du réglage ajusté des paramètres de balayage ;
    si le réglage des paramètres de balayage pour la fraction présente n'est pas inférieur à la limite des paramètres de balayage, alors déterminer si une caractéristique du patient excède un seuil de caractéristique ; et
    si la caractéristique du patient excède le seuil de caractéristique, alors ajuster le réglage des paramètres de balayage pour la fraction ultérieure, le ratio de diffusion par rapport à primaire durant la fraction ultérieure étant inférieur à celui durant la fraction présente sur la base du réglage ajusté des paramètres de balayage.
  11. Dispositif d'administration de radiothérapie (10) comprenant :
    un système de portique rotatif (12) positionné au moins partiellement autour d'un support de patient (18) ;
    une première source de rayonnement (20) accouplée au système de portique rotatif (12), la première source de rayonnement (20) étant conçue comme source de rayonnement thérapeutique (22) ;
    une seconde source de rayonnement (30) accouplée au système de portique rotatif (12), la seconde source de rayonnement (30) étant conçue comme source de rayonnement d'imagerie (32) ayant un niveau d'énergie inférieur à la source de rayonnement thérapeutique (22) ;
    un détecteur de rayonnement (34) accouplé au système de portique rotatif (12) et positionné pour recevoir un rayonnement (32) de la seconde source de rayonnement (30) ; et
    un système de traitement de données conçu pour :
    recevoir (305) une mesure précédente de diffusion de fraction à partir d'une fraction précédente ;
    recevoir (310) une mesure présente de diffusion de fraction à partir d'une fraction présente, un ratio de diffusion par rapport à primaire durant la fraction présente étant supérieur à celui durant la fraction précédente, une configuration de balayage de la fraction présente étant assouplie par rapport à une configuration de balayage de la fraction précédente, la configuration assouplie de balayage étant associée à un ratio supérieur de diffusion par rapport à primaire par rapport au ratio de diffusion par rapport à primaire pour la fraction précédente ; et
    déterminer (330) une estimation présente de diffusion de fraction sur la base de la mesure présente de diffusion de fraction et de la mesure précédente de diffusion de fraction ;
    reconstruire une image de patient pour la fraction présente sur la base de l'estimation présente de diffusion de fraction ; et
    administrer une dose de rayonnement thérapeutique (22) au patient par l'intermédiaire de la première source de rayonnement (20) sur la base de l'image du patient durant une IGRT adaptative.
EP19824063.2A 2018-11-30 2019-11-25 Procédé et appareil pour la reconstruction et la correction d'image à l'aide d'information inter-fractionnaire Active EP3886706B1 (fr)

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US201862773700P 2018-11-30 2018-11-30
US201862773712P 2018-11-30 2018-11-30
US201962796831P 2019-01-25 2019-01-25
US201962800287P 2019-02-01 2019-02-01
US201962801260P 2019-02-05 2019-02-05
US201962813335P 2019-03-04 2019-03-04
US201962821116P 2019-03-20 2019-03-20
US201962836357P 2019-04-19 2019-04-19
US201962836352P 2019-04-19 2019-04-19
US201962843796P 2019-05-06 2019-05-06
US201962878364P 2019-07-25 2019-07-25
PCT/US2019/063087 WO2020112685A1 (fr) 2018-11-30 2019-11-25 Procédé et appareil pour la reconstruction et la correction d'image à l'aide d'information inter-fractionnaire

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EP19824063.2A Active EP3886706B1 (fr) 2018-11-30 2019-11-25 Procédé et appareil pour la reconstruction et la correction d'image à l'aide d'information inter-fractionnaire
EP23215814.7A Pending EP4310864A3 (fr) 2018-11-30 2019-11-25 Procede et appareil permettant d'ameliorer l'estimation et la correction de la diffusion dans l'imagerie
EP19824057.4A Active EP3886710B1 (fr) 2018-11-30 2019-11-25 Système de tomodensitométrie et procédé d'amélioration d'image faisant intervenir l'image précédente
EP19888415.7A Pending EP3886711A2 (fr) 2018-11-30 2019-11-25 Procédés de balayage et système de tomographie optimisés utilisant des données de région d'intérêt
EP19824058.2A Active EP3886708B1 (fr) 2018-11-30 2019-11-25 Procédé et appareil d'estimation de diffusion dans une tomodensitométrie à faisceau conique
EP19824056.6A Pending EP3886979A1 (fr) 2018-11-30 2019-11-25 Tomographie assistée par ordinateur à faisceau hélicoïdal intégré dans un dispositif de traitement par rayonnement guidé par l'image
EP19824062.4A Pending EP3886709A2 (fr) 2018-11-30 2019-11-25 Balayages de tomographie par ordinateur à passages multiples à des fins de flux de travail et de performance améliorés
EP19824059.0A Pending EP3886714A1 (fr) 2018-11-30 2019-11-25 Ajustement de diffusion asymétrique pour une lecture de panneau optimale dans une tomodensitométrie à faisceau conique
EP19818497.0A Pending EP3886707A1 (fr) 2018-11-30 2019-11-25 Tomodensitométrie à faisceau conique hélicoïdal avec un détecteur décentré
EP19824061.6A Pending EP3886705A1 (fr) 2018-11-30 2019-11-25 Appareil et procédés d'imagerie à champ de vision échelonnable en utilisant un système à sources multiples

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EP19824057.4A Active EP3886710B1 (fr) 2018-11-30 2019-11-25 Système de tomodensitométrie et procédé d'amélioration d'image faisant intervenir l'image précédente
EP19888415.7A Pending EP3886711A2 (fr) 2018-11-30 2019-11-25 Procédés de balayage et système de tomographie optimisés utilisant des données de région d'intérêt
EP19824058.2A Active EP3886708B1 (fr) 2018-11-30 2019-11-25 Procédé et appareil d'estimation de diffusion dans une tomodensitométrie à faisceau conique
EP19824056.6A Pending EP3886979A1 (fr) 2018-11-30 2019-11-25 Tomographie assistée par ordinateur à faisceau hélicoïdal intégré dans un dispositif de traitement par rayonnement guidé par l'image
EP19824062.4A Pending EP3886709A2 (fr) 2018-11-30 2019-11-25 Balayages de tomographie par ordinateur à passages multiples à des fins de flux de travail et de performance améliorés
EP19824059.0A Pending EP3886714A1 (fr) 2018-11-30 2019-11-25 Ajustement de diffusion asymétrique pour une lecture de panneau optimale dans une tomodensitométrie à faisceau conique
EP19818497.0A Pending EP3886707A1 (fr) 2018-11-30 2019-11-25 Tomodensitométrie à faisceau conique hélicoïdal avec un détecteur décentré
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US11413002B2 (en) 2022-08-16
CN113164138B (zh) 2024-10-11
EP3886711A2 (fr) 2021-10-06
CN113164139A (zh) 2021-07-23
US11375970B2 (en) 2022-07-05
EP3886706A1 (fr) 2021-10-06
US20200175733A1 (en) 2020-06-04
JP2022509680A (ja) 2022-01-21
EP3886705A1 (fr) 2021-10-06
EP3886714A1 (fr) 2021-10-06
US20200170596A1 (en) 2020-06-04
EP3886703B1 (fr) 2023-12-20
CN113164758B (zh) 2024-08-06
JP2022509006A (ja) 2022-01-20
CN113164148A (zh) 2021-07-23
JP7408657B2 (ja) 2024-01-05
US11191511B2 (en) 2021-12-07
JP2022510958A (ja) 2022-01-28
JP2022509005A (ja) 2022-01-20
CN113164144A (zh) 2021-07-23
JP2022509859A (ja) 2022-01-24
US11154269B2 (en) 2021-10-26
US20200170600A1 (en) 2020-06-04
EP3886707A1 (fr) 2021-10-06
WO2020112677A3 (fr) 2020-11-05
US20220000443A1 (en) 2022-01-06
WO2020112685A1 (fr) 2020-06-04
CN113164136A (zh) 2021-07-23
US11224396B2 (en) 2022-01-18
WO2020112673A1 (fr) 2020-06-04
EP3886709A2 (fr) 2021-10-06
EP3886710B1 (fr) 2024-01-24
WO2020112676A1 (fr) 2020-06-04
CN113164138A (zh) 2021-07-23
EP3886710A1 (fr) 2021-10-06
EP3886979A1 (fr) 2021-10-06
US20200170607A1 (en) 2020-06-04
CN113164132A (zh) 2021-07-23
US11337668B2 (en) 2022-05-24
JP2022510095A (ja) 2022-01-26
US20200170601A1 (en) 2020-06-04
WO2020112674A1 (fr) 2020-06-04
JP2022509306A (ja) 2022-01-20
WO2020112684A3 (fr) 2020-12-17
JP7458389B2 (ja) 2024-03-29
WO2020112677A2 (fr) 2020-06-04
US11179132B2 (en) 2021-11-23
US20200170598A1 (en) 2020-06-04
US20220257209A1 (en) 2022-08-18
EP3886704B1 (fr) 2024-01-31
CN113164758A (zh) 2021-07-23
JP7534038B2 (ja) 2024-08-14
CN113164135A (zh) 2021-07-23
WO2020112684A2 (fr) 2020-06-04
US11364007B2 (en) 2022-06-21
CN113164129A (zh) 2021-07-23
JP2022510096A (ja) 2022-01-26
EP4310864A3 (fr) 2024-04-03
JP2024100832A (ja) 2024-07-26
US11638568B2 (en) 2023-05-02
CN113164143A (zh) 2021-07-23

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